EP0952867B1 - Vorrichtung zur lokalen verabreichung von fest-oder halbfesten pharmazeutischen zusammensetzungen - Google Patents

Vorrichtung zur lokalen verabreichung von fest-oder halbfesten pharmazeutischen zusammensetzungen Download PDF

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Publication number
EP0952867B1
EP0952867B1 EP97948983A EP97948983A EP0952867B1 EP 0952867 B1 EP0952867 B1 EP 0952867B1 EP 97948983 A EP97948983 A EP 97948983A EP 97948983 A EP97948983 A EP 97948983A EP 0952867 B1 EP0952867 B1 EP 0952867B1
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EP
European Patent Office
Prior art keywords
formulation
assembly according
active principle
solid
plga
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French (fr)
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EP0952867A2 (de
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Roland Cherif-Cheikh
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Ipsen Pharma SAS
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Societe de Conseils de Recherches et dApplications Scientifiques SCRAS SAS
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00—Medicinal preparations characterised by special physical form
    • A61K9/0012—Galenical forms characterised by the site of application
    • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61D—VETERINARY INSTRUMENTS, IMPLEMENTS, TOOLS, OR METHODS
    • A61D7/00—Devices or methods for introducing solid, liquid, or gaseous remedies or other materials into or onto the bodies of animals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
    • A61M37/0069—Devices for implanting pellets, e.g. markers or solid medicaments
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P29/00—Non-central analgesic, antipyretic or antiinflammatory agents, e.g. antirheumatic agents; Non-steroidal antiinflammatory drugs [NSAID]

Definitions

  • the present invention relates to a therapeutic method for the targeted treatment of non-liquid galenical formulations as well as the preparation and the device designed for the implementation of the method.
  • PA active ingredient
  • the local treatment compared to a general treatment makes it possible above all to reduce the doses and the secondary effects notably related to PA in sites of the organism where its presence is either useless or harmful.
  • the local administration of a drug makes it possible, therefore, to improve the therapeutic index of the product while reducing if necessary its general toxicity and the risks of systemic effects.
  • Topical cutaneous, ocular, nasal-sinus, pulmonary or gastric or rectal forms were the first non-parenteral forms to use local administration.
  • formulation deposition site is more difficult to access or requires an invasive form and when the treatment has to be repeated, or even more so, chronic, even if the advantage of targeting is known, in practice its use is hurts the difficulty or even the discomfort of a repeated therapeutic gesture.
  • This delayed form improves compliance since the observance of the treatment no longer depends on the patient or the nursing staff but on the preparation. This prolonged effect thus improves the comfort of the patient who is no longer constrained to his treatment, and who thus receives a regular dose permanently and not variable depending on the medication taken.
  • the development of the forms delays has led specialists to consider their local uses especially in the case mentioned above where the deposit site is more difficult to access.
  • the delay form avoids, then, to have to repeat the administrations or, even more, the surgical gesture.
  • This solution is particularly useful for products that are rapidly metabolized or have a short half-life when administered systemically.
  • cancers and in particular solid tumors, are prime candidates for these local forms which make it possible to reduce the total injected doses of cytotoxic or antineoplastic compound, while increasing the concentration in the tumor zone to be treated. This is likely to avoid the serious side effects of this type of treatment.
  • Matrix Pharmaceutical offers a delayed preparation based on collagen that can be injected intratracheally (IntraDose CDDP-Cisplatin). This formulation is administered in cancers or skin lesions using a 3 cc syringe and possibly a biopsy needle for less accessible areas. Under a viscous liquid volume of up to 2ml, it is therefore limited to sites at first relatively easy (peripheral) or post-surgical treatments.
  • the Gliadel form (Guilford) for its part describes a formulation containing host-shaped polyanhydride containing Carmustine and which may, for example, be deposited at the time of surgery in a brain tumor (glioblastoma).
  • Chemoembolization procedures are also used, which consist of injecting suspensions (microspheres), gels or glues with their solvent into vessels, which can obstruct a feeder vascular pathway and release a PA at the level of the vessel. a tumor. The occlusion is obtained by deposit after departure of the injection vehicle.
  • This technique uses percutaneous transluminal angioplasty catheters to introduce fluid into the vessel.
  • the ®Ocusert (Alza) system is a flexible and oval ocular insert which constitutes a delay reservoir device comprising an ethylene-vinyl acetate copolymer membrane and which may contain, for example, pilocarpine.
  • This device is placed in the conjunctival cul-de-sac and releases its product in a zero order profile.
  • the delay form makes it possible to significantly reduce the dose required for the same effect on the intraocular pressure.
  • the therapeutic efficacy of pilocarpine in the treatment of glaucoma is thus 8 to 10 times better thanks to the use of a form delay compared to drops in local.
  • U.S. Patent No. 3,545,439 discloses an intra-vaginal delay form consisting of a ring made with a silicone elastomer and which releases a medicament while Several weeks.
  • the local delay administration on the vaginal mucosa also allows, according to P.A., to obtain a general effect (contraception).
  • the medical device described by Bukh M machineée allows the introduction into a body cavity of a matrix delay form made of a substance slightly penetrable by water and containing a PA
  • the delay form associated with the device thus delivers P.A. at the local level and for the duration of insertion of said device. It describes, for example, a catheter for the urethra opening into the bladder associated with an antibiotic delay form likely to prevent urinary tract infections.
  • CRBARD Transurethal delivery kit
  • a formulation Transurethal delivery kit which is a syringe containing a solution of collagen in glutaraldehyde that can be easily injected into submuscocal in volumes of 2, 5 to 7.5 ml which constitute implants without active principle in the context of a plasty against incontinence.
  • Part of the device can sometimes be left locally and therefore be associated with a delay form.
  • This is the case of the "stents" used, for example in angioplasty, to avoid restenosis, which can be covered with a layer containing an active ingredient sometimes with a delay effect.
  • heparin inhibits the proliferation of smooth muscle cells after endothelial injury. Its systemic administration, in subcutaneous or local delayed form external to the vessel, always leads to a decrease in neointimal proliferation, but the local form is the only one that does not cause systemic disturbances of coagulation.
  • Osmotic pumps that are used to validate prolonged local administrations could also be mentioned, with the major disadvantage of their surgical implantation. For this reason, they are not currently used in humans.
  • Each of these solutions can treat only one or more particular cases in a specific site of the body.
  • Localization vectorization is sometimes referred to as first-generation compared to "second-generation” prodrugs and vectors (liposomes %) or to recognition systems macromolecular or activation "specific site” said third generation.
  • WO 84/00304 discloses an assembly comprising a portion intended to be placed inside the body of the patient and containing an implant, and positioning means for bringing the implant to the location of the deposit site, means for insertion to release the implant in this site, after which the device can be removed leaving the implant in place, the implant being for example an implant intended to deliver a substance diffused systemically, for the treatment of the deficiency in estrogen after menopause.
  • the aim of the invention is to propose a method that overcomes the major disadvantages of local administration or vectorization by flexible endoscopic (fibroscopy) or rigid (endoscope) and interventional radiology (active catheter or non-active catheter) surgery techniques.
  • the solid and semi-solid non-dispersed formulations have the advantage of offering a minimum volume for a quantity of AP corresponding to a treatment dose.
  • the solid and semi-solid delay forms can, thus, allow several days of treatment in one volume. of some micro-liters.
  • the local administration of a treatment makes it possible to significantly reduce the total therapeutic dose for the same effect.
  • the invention therefore proposes a method, a device and a formulation adapted to the progress and miniaturization of pharmaceutical and medical technologies.
  • the subject of the invention is an assembly for the implantation and insertion in a precise deposition site of the body of a solid or semi-solid formulation such that it can persist for a certain duration in the site, and containing a dose of active ingredient, comprising a device having a part intended to be placed inside the body of the patient with means for conditioning the solid or semi-solid form, positioning means for bringing these conditioning means up to at the deposition site, injection or insertion means at this deposition site, and withdrawal means after injection or insertion, and a part left outside with means for activating the functions of the device characterized in that it comprises, in said device, a formulation to be delivered, of solid or semi-solid consistency having a shape that can be trapped in an anatomical cavity of the body, avoiding the placement or removal of the formulation, said formulation comprising only one dose of an active ingredient to a limited treatment in a targeted area of the body through said cavity, and being contained in said conditioning means.
  • the pharmaceutical and medical aspects of the invention come together in the search for a thin and miniaturized system that can be easily positioned and activated in all areas of the body from transdermal percutaneous angioplasty catheters, endoscopes or any other invasive device that is sufficiently fine and long to reach the deposit zone.
  • the (fine and long) form of the formulation in the administration device facilitates its local repository. This characteristic of the system under its pharmaceutical and medical aspect will allow its general use.
  • insertion is understood to mean a form deposited on the surface and by implantation, an injection into a tissue, the targeted or even prolonged treatment may be inserted inside a natural cavity of the organism if this is likely to occur. to act as a natural reservoir, that is to say if the shape of the drug deposit allows it to stay in the body cavity at least for the duration of its release.
  • This form can be either the elongate shape studied to facilitate its deposition with the device, or its evolution once deposited.
  • the shape of the device and the formulation is therefore not a priori adapted to the insertion zone as Ocusert can be, the vaginal ring or stents.
  • the form of the formulation can however evolve after filing to facilitate its local maintenance. After its deposit, the formulation is not associated with all or part of the deposit device but left alone at the deposit site.
  • targeted or prolonged treatment may also be implanted within a target tissue of the body. organism, to allow its deposit over the release period.
  • This implantation may be performed with the device associated with conventional tools, transcutaneously, vascular or cavitary in a mucosa or a wall of the body or surgically in a target tissue.
  • the insertion of the delay form will allow a local, superficial or external treatment, but also targeting for effect in depth, or even for systemic effect, for example with a deposit on the mucous membranes.
  • implantation of the delayed form will allow general treatment but also targeted treatment by local hyperconcentration or excretion.
  • insertion as the implementation could be a systemic solution, an internal local solution or, finally, an external targeting solution.
  • the immediate solid or semi-solid or retard formulations used in the process of the invention may be any solid or semi-solid formulations that can be manufactured or packaged in the form and volume compatible with the method and the device. injection.
  • the solid or semi-solid formulations may be preferably formulations made from biodegradable excipients such as, for example inorganic salts (calcium, magnesium, bismuth, zinc); lipids; carbohydrates (polysaccharides, sucrose, glucose, agarose, dextrin, cyclodextrin and mixtures); proteins (gelatin, modified collagen, albumin, casein, derivatives and mixtures); natural and synthetic polymers (polyisobutyric acid, polylactic acid, polyglycolic acid, polylactide-polyglycolide copolymer (PLGA), polyester, polycaprolactone, polyethylene glycol, polypropylene glycol, ®Pluronics, polyanhydrides and mixtures thereof).
  • biodegradable excipients such as, for example inorganic salts (calcium, magnesium, bismuth, zinc); lipids; carbohydrates (polysaccharides, sucrose, glucose, agarose, dextrin, cyclodextrin and mixture
  • the solid or semi-solid formulations may be made without excipient or structured with small amounts of injectable excipient such as mannitol, hyaluronic acid, cellulose derivatives ...
  • the semi-solid formulations may be made by mixing P.A. with or without an excipient, with water, an organic solvent, oil or any other injectable liquid capable of giving the semi-solid form.
  • Solid or semi-solid formulations will be either immediate formulations or delayed formulations.
  • the immediate solid formulations can be made as indicated in the SCRAS (Delivery of Solid Drug Compositions) patent. WO96 / 07397 ).
  • the semi-solid formulations and solid delays may be carried out according to the formulation and the process claimed by the SCRAS patent (Sustained Release of Peptides from Solid and Semi-solid Pharmaceutical compositions WO96 / 07398 whose contents are incorporated by reference).
  • the solid or semi-solid formulations will advantageously be produced according to processes allowing a high concentration of active ingredient greater than 20% or even greater than 40%, preferably greater than 50% and up to 100% of P.A.
  • the solid, non-dispersed formulations according to the invention will have a thin and elongated shape: rod, implant, pellet, stick or needle, so that they can be introduced inside the implantation device which can -even, if necessary depending on the depth of the injection into the body, be inside an endoscope or a catheter.
  • the dispersed solid formulations (powders, spheres) should be able to be arranged longitudinally in the device.
  • the solid formulations in the device will thus preferably have a maximum diameter of 3 mm and advantageously a diameter of less than 2.5 mm or even a diameter of less than 2 mm, preferably less than 1 mm.
  • the diameter of the solid forms can be even smaller and up to 0.1 mm .
  • the smaller diameters may, in some cases, have a technical advantage to facilitate deep local implantation;
  • a larger diameter will not have the same disadvantages (especially in terms of comfort of the patient) than in the case of superficial injections type trocars (Zoladex, registered trademark by Zeneca) or mini -troctors (Auto-injector, Retro-injector: Needle-less Parenteral Introduction Device WO96 / 08289 or because the use of medical devices also requires local or general anesthesia, or because the deep implantation area is less sensitive than the skin.
  • the solid forms may have a length of a few centimeters, generally less than 3 cm and preferably less than 2 cm and adapted to the space in the deposition zone.
  • the solid forms will preferably be cylindrical and obtained by extrusion techniques.
  • the semi-solid forms will have a sufficiently high viscosity to contain a high concentration of PA (preferably greater than 20%) and remain homogeneous while allowing deep injections through the needle of the device of the invention. .
  • the semi-solid forms may be gels, oils, pastes or any other semi-solid dispersion of an AP in a liquid vehicle.
  • the semi-solid forms will have a low total volume generally less than 300 .mu.l and preferably less than 100 .mu.l or even less than 50 .mu.l.
  • the method and devices according to the invention will preferentially use injectable excipients biodegradable or normally removed or solubilized in body fluids.
  • the method may use devices or formulations based on non-biodegradable biocompatible biomaterials when the site and the depositing tools will easily allow the withdrawal of said device or said formulation after its operation, that is to say rather for inserts only for implants.
  • the device or formulation should have a fine and elongated shape, like other solid forms compatible with deep local administration.
  • the devices according to the invention correspond to the solid or semi-solid formulations associated with the insertion device or localized deep implantation.
  • the device according to the invention for the implantation or the insertion of an active principle in a solid or semi-solid formulation into a precise deposition site of the organism, is characterized in that it comprises a part placed within the body of the patient with means for conditioning the solid or semi-solid form, positioning means to the site deposition, injection or insertion means at this deposition site and withdrawal means after injection or insertion, and a part left outside with means for activating the functions of the device.
  • the devices can be used directly or associated with local therapy medical instruments (endoscope, fiberscope, tube, catheter, nail, aerator, cannula, perforator, trocar ).
  • local therapy medical instruments endoscope, fiberscope, tube, catheter, nail, aerator, cannula, perforator, trocar .
  • the devices will be introduced locally and will allow the insertion or implantation of semi-solid or solid forms. They will be withdrawn immediately after this deposit.
  • the devices used, according to the method of the invention for deep local administration of solid or semi-solid formulations will be polyvalent and of low volume with a fine and elongated adapted form.
  • the devices will therefore preferably have a maximum diameter of 3 mm and advantageously a diameter of less than 2.5 mm or even less than 2 mm. Depending on the formulation, the diameter of the device may be even smaller and up to 0.3 mm.
  • the insertion or implantation device may, as a conventional tool (biopsy clip style) occupy the instrument channel, which releases the fluid introduction channel or even allows its elimination.
  • the devices may have a diameter less than 2 mm and, for example, 1.7 mm as some instruments.
  • the insertion or implantation device may, like the stent insertion device, occupy the channel and be activated from the outside in situ.
  • the device may have a diameter less than 2.5 mm and, for example, 2 mm as some stents.
  • the insertion or implantation device may, like the perforation device, occupy the trocar lumen.
  • the device may have a diameter less than 3 mm and, for example, 2.5 mm as some perforators.
  • the device for administering a solid form 1 represented in FIG. 1 comprises a tubular guide 2 containing a piston 3 that can push outside the guide 2 the solid form 1 contained at the end of the latter.
  • the guide 2 and the piston 3 are provided, at their opposite ends, with respective flanges 4, 5 of manual manipulation.
  • FIG. 2 illustrates a possible example of an invasive system in the body of a patient for the implementation of the device for administering the solid form 1 of FIG. 1.
  • the invasive system is in the example of FIG. 2 a trocar 6 containing a perforating mandrel 7, if access to the natural cavity of the body used as a release reservoir of the solid formulation 1, requires perforation of internal tissues.
  • the invasive system is shown partially introduced internally in the body in its part to the right of the plane L, while its left part remains externally.
  • the invasive system may be an endoscope, a fiberscope or a catheter (not shown).
  • the invasive system used is introduced into the body cavity (sinus of the face, esophagus, trachea, vessel ...), thanks to the perforating mandrel 7 in the case of a system such as that of Figure 2. Then the mandrel 7 is removed from the trocar 6 (or the endoscope, catheter, ...) and the administration device of Figure 1 is introduced inside the trocar 6 ( Figure 3), until the collar 4 of the guide 2 comes into abutment against the curved annular end 8 of the trocar 6.
  • this device is provided for the case of an injection of said device into a tissue, a wall or mucosa from an internal invasive system already engaged in a cavity as shown in the drawings, but also from an invasive system engaged in an internal tissue.
  • the invasive system comprises a tubular piece 50 partially engaged in the tissue through the surface P 'thereof, and a tubular guide 11 which may be a fiberscope or an endoscope, in which a catheter 12 may be mounted.
  • a guide of the delivery device formed by a needle 13 and a piston 14 for extracting the solid form 9 in the tissue 17.
  • the device comprises two removable stops (10, 15), the first of which is a sleeve disposed in a pusher 20 coaxial with the piston 14, this abutment 10 and the pusher being truncated longitudinally (FIG. 8); the second is a tubular piece 15, also truncated (FIG. 6), interposed between the catheter 12 and the pusher 20.
  • the injection of the delivery device 13, 14, 9 can be obtained by moving the guide back, but is preferably performed as illustrated in Figures 7 to 10, as follows.
  • the stopper 15 is removed; the needle 13 is moved by means of the pusher 20 containing the abutment 10 (FIG. 7).
  • the needle 13 may have at its end a curved shape 13a obtained by releasing an elastic preload of the needle 13 in the guide. Once released from the stress of the guide, the curved end 13a facilitates the oblique injection of the solid form 9 into the wall or the mucosa 17. This angle between the needle and the guide can be obtained or adjusted by any other mechanism usually used by these devices.
  • the device of Figures 5 to 10 may also allow the administration of a semi-solid.
  • the delivery device illustrated in FIGS. 11 to 16 is similar to that of FIGS. 5 to 10 and does not differ in that the piston 14 acts on a non-solid form 18, similar to a micro-syringe. to the tip of the injection device.
  • the invasive system 9, 11, 12 can be engaged in an internal tissue 17.
  • the method of administration here consists in injecting, by pushing outside the guide 9, 11, 12, the administration device consisting of the needle 13, the piston 14 and the semi-solid form 18.
  • L Needle 13 may optionally be curved as in the embodiment of Figures 5 to 10.
  • the piston 14 is moved in the needle 13 to inject the semi-solid 18 (Figure 14) in the same manner as in the previous embodiment.
  • FIGS. 1 to 16 will make it possible to illustrate the methods of administration for various specific treatments described below. These different specific treatments according to the method of the solid or semi-solid local administration invention involve the implementation of the method to be applied and thus offer some new therapeutic solutions that form part of the invention. These various examples illustrate the possible field of application of the invention, but do not constitute an exhaustive list of applications of the method and are therefore not limiting.
  • the formulation is not, in its composition or in its form, studied for precise vectorization.
  • the formulation is studied for a tool or device adapted to internal local administration and which allows remote injection or insertion in situ.
  • the method will be able to use, in this galenical form and with these tools, conventional APs and especially those having already demonstrated their interest in local administration, or whose local interest can be deduced from the mode. the action of the PA, even if its use in this form does not exist yet, especially because it could not be easily implemented without the contribution of the invention.
  • the following examples illustrate the possibilities of this process.
  • the method, formulations and devices allow administration into cavities of the body and intra-tissue. Whatever the cavity or the tissue, the advantage is to be able to bring the formulation to the deposition site by avoiding or reducing the tissue lesions.
  • Intra or peripinous inserts or implants may convey PA in the mucus thanks to ciliary mucosal flows or allow its systemic local diffusion by contact. We can also consider a general action by gradual diffusion to the disgetive pathways for drugs requiring daily doses at low doses.
  • Local corticosteroids are a good example of a local action product with general disadvantages.
  • existing local treatments drops, spray, etc.
  • the necessary persistence of the PA locally involves frequent applications.
  • This therapeutic process makes it possible to reach this key zone of the naso-sinus pathology.
  • the tympanic cavity can be treated locally.
  • the solid retard form or implanted or inserted semi-solid will be in contact with this mucous membrane which secretes and covers itself with a mucus circulating from the meatus towards the nasal fossae, and evacuated towards the cavum while passing in contact with the tubular bead and the Eustachian tube.
  • the method will make it possible, for example, to increase and maintain the concentration of therapeutic product in the unicellular groove, which is responsible for particularly inflammatory pathologies.
  • a device according to the diagram of FIG. 1 will be used which can be positioned thanks to the conventional drainage tools of otolaryngology (ENT; trocars, tubes). It is also possible to inject the formulation into the mucosa of the nasal cavities, into the cones or into the tubular bead by means of the devices presented in FIGS. 5 to 16. Depending on the zone of deposition and the formulation, the action will therefore preferably be external, intra -tissular or systemic.
  • ENT it will thus be possible to treat, for example, by corticotherapy, nasosinus polyposis, allergic or non-allergic rhinitis, certain non-infectious otitis or sinusitis, etc.
  • corticotherapy nasosinus polyposis
  • allergic or non-allergic rhinitis certain non-infectious otitis or sinusitis
  • anti-inflammatory treatments we can practice antibiotic, anti-allergic, immunostimulant treatments, etc ...
  • Dexamethasone stents 15% stamped phosphate in PLGA 50-50 it is possible, for example, to manufacture Dexamethasone stents 15% stamped phosphate in PLGA 50-50 according to the following steps: weighing of the raw materials, mixing of the two powders, extrusion, dosing, packaging and sterilization.
  • the implant obtained may have an average diameter of 2.4 mm for a length of 12.5 mm. It may be introduced into the maxillary sinuses using the device shown schematically in Figure 1. It may also be implanted in the mucosa of the cornet using the device shown schematically in Figures 5 to 10.
  • This solid formulation is a 1-month-delay formulation that contains 7.5 mg of Dexamethasone and averages 0.5 mg / day with one implant in each sinus.
  • a polymeric form PLGA 75-25
  • Hydromed type a reservoir form
  • These delayed preparations may be used as an outpatient for patients suffering, for example, from chronic nasal obstruction.
  • the medical procedure for intrasinusal administration will be similar to standard ENT procedures, which can be performed in the doctor's office: trocar puncture with or without anesthesia.
  • the approach may be prepared or not (metatomy, nails, drains or other).
  • the deep injection located in the cornet or mucous membranes of the nasal cavity will also be easy thanks to the device associated or not with the usual tools of endoscopic exploration.
  • the local administration is shallow.
  • the distance between the external zone and the internal deposition may be even shorter or much larger.
  • Delayed corticosteroids are already used in rheumatology.
  • a local intra- or peri-articular injection with low-volume deposition of delay form (corticosteroids, anti-inflammatories) at the site of inflammation (tendonitis, bursitis, non-infectious arthritis, osteoarthritis). .
  • the injection is practically superficial and does not require tools outside the delivery device for semi-solid or micro-volume solids.
  • dermopeptin (BIM 23014C) may be used in a semi-solid 20% retarded form in water and in a volume of 20 microliters, ie a total dose of 4 mg of Somatuline.
  • the formation may be injected into the keloids or melanomas, creating a high and prolonged local concentration from a diffusion gradient zone at the injection site.
  • the treatment may be associated with a cytotoxic (Type 5FU or cisplatin) whose diffusion will be regulated by the same local form and whose local concentration will be very high with a very low total dose.
  • cytotoxic Type 5FU or cisplatin
  • SMA Shape memory Alloy
  • fibroscope active catheter-type tools and with specialties such as interventional radiology or endoscopic or robotic surgery.
  • the solid or semi-solid forms according to the invention have the advantage, compared to the Gliadel type local treatment, of being able to be applied without trepanation at the superficial level, but also in depth thanks to stereotactic, endoscopic and robotic neurosurgery.
  • Matrix can be treated the same with these microdosages.
  • the volume advantage allows vectorization in all sites and avoids the risk of propagation caused by the injection of a liquid volume of a few milliliters.
  • the method and devices, according to the invention, associated with the fiberscope or any other direct or indirect imaging solution, allow the administration in the organic walls.
  • the bladder is operated by the urethral route, it is possible to imagine the implantation of a treatment (prophylaxis, antibiotic, etc.) in the thickness of the urethra.
  • a pulmonary treatment either by deposition of a solid or semi-solid form in the lung or by implantation in the mucosa, bronchi or trachea, according to local tolerance requirements within the lungs.
  • the solid form may be dispersed (powder or sphere).
  • glucocorticosteroids for example, to replace the preventive treatment with inhaled glucocorticosteroids in mild or moderate recent diagnostic asthma.
  • a delayed form of 0.4mg of daily Budesonide which will be secreted into the flow if the form is implanted, and which will be conveyed by the moisture to the bottom of the pulmonary alveoli.
  • This preventive treatment at low dose, without side effects, does not pose any more problem of compliance especially in children.
  • Such a form may have a duration of 1 to 3 months, or more if necessary.
  • treatment of varicose veins may be considered from a local form and injected into the wall.
  • tumors at this level which are well individualized and are currently treated, for example by PDT (photochemotherapy)
  • PDT photochemotherapy
  • the method of local administration of solid or semi-solid forms involves the prolonged presence of a local deposition of PA. If necessary, it may be possible to add to the formulation products that promote local tolerance at the disposal site. For example, very low percentage of Dexamethasone, Indomethacin, Heparin or any other PA may be added to avoid an undesirable local effect.
  • the mucous membranes or the walls are more permeable than the skin and there are systems of patches or bioadhesives that apply to the mucous membranes (in particular the mouth or the nose) and which allow a systemic passage of the AP.
  • the disadvantage is sometimes the non-persistence of the formulation in contact with the mucosa.
  • the prolonged presence of the administration according to the method at the local level of the mucous membranes or the internal walls may therefore have an advantage in the search for a topical form with systemic activity.
  • a deep local form may advantageously be the site of a systemic diffusion with respect to the oral or nasal mucosa, for example, which would not allow prolonged topical deposition.
  • PAs used local anesthetics, anticoagulants
  • PAs used can be administered in a solid or semi-solid form with here, again, the advantage of a micro-volume in adequacy with the reduced space of intervention, and the possibility of administration via the instrumental access channel.
  • any other solid or semi-solid delay form and in particular PLGA implants can be used with other peptides, recombinant proteins (interferon), polyclonal or monoclonal antibodies, oligonucleotides or antisense polynucleotides, etc.
  • solid formulations or implants that can be used for local administration of the active ingredient as described above are also suitable, because of their long, thin shape and small diameter, for other types of conventional administrations, for example for systemic treatment with cutaneous or intramuscular injection.
  • said solid or implant formulations in particular with a PLGA excipient, having a very high concentration of active principle, as described above, whether it is soluble or insoluble, and in particular those having a concentration of active ingredient of between 40 and 100%, and preferably greater than 50%, make it possible to obtain, in vivo, extremely long release times, from one month to three months and more, and release rates very regular, even constant, being made in fine elongate form, of diameter or transverse size less than or equal to 3 mm, for example 2.5 or 2 mm, or even 1 mm or less, while they dissolve very quickly in vitro, and whether they are used for local action or not.
  • the inventors have furthermore discovered that, in one form, in homogeneous distribution of excipient, in particular PLGA, it was possible to obtain a delay formulation in a non-matrix mode in which the role played by the excipient was different; This leads to more advantageous formulations whose characteristics are different, which clearly distinguishes them from the existing matrix forms.
  • non-matrix forms may be described as matrix forms of active ingredient in which the excipient is dispersed.
  • the PLGA matrix forms used to date can be either dispersed forms (microparticles) or non-dispersed forms (implants).
  • the “reservoir” forms use a barrier or diffusion membrane between the active ingredient and the medium that will serve to regulate the release of this active ingredient.
  • the drug can be inside the reservoir in a solid, semi-solid or liquid form. It may be in solution or dispersed in an excipient.
  • the membrane ensures by its porosity the controlled passage of the active principle to the outside.
  • hydrophilic membranes in cross-linked hydroxyethyl poly-methacrylate pHEMA, Hydro Med Sciences.
  • the “reservoir” forms make it possible to obtain a relatively constant release level of order 0.
  • the main disadvantage of these reservoir techniques is the need to remove the biocompatible but non-biodegradable implant after release of the active ingredient.
  • the matrix forms use a polymer matrix or weft in which the active ingredient is trapped to be released by diffusion, erosion or combination of both phenomena.
  • the non-biodegradable matrix forms such as, for example, PDMS silicone-type hydrophobic polymer implants (Norplant, progestational hormones), function only by diffusion. This mode of operation can result in decreasing first order release when the diffusion distance increases.
  • biodegradable matrix forms do not have this disadvantage since the polymer matrix is eliminated by the body.
  • this elimination or erosion can participate in the regulation of the release of the active ingredient to obtain a constant release.
  • the most widely used matrix biodegradable forms currently use polymers of lactic acid or glycolic acid, copolymers of lactic acid and glycolic acid (PLGA) or mixtures thereof.
  • EP 52510 discloses a PLGA formulation with encapsulation of LHRH or the like which may be a dispersed form of microcapsules produced by coacervation, the particularity of which is the distribution of the active ingredient in the center of the microcapsule with a layer of peripheral PLGA.
  • dispersed or non-dispersed peptide and PLGA formulations are known, such as implants, in which the active ingredient is uniformly distributed to the surface and using a specific PLGA so that the two release phases (diffusion and degradation) overlap without there being any interruption in the release of the active ingredient.
  • the control of the retardation effect is obtained by matrix mixing of the PLGA and the active ingredient so as to allow the polymer matrix to play its role as a release barrier for the active ingredient, or even a role in the physicochemical interactions between the active ingredient and the polymer matrix.
  • this mode of release requires a dispersion of the active ingredient in the biodegradable polymer matrix, so as to isolate the active agent charge zones to the external environment and retain them within the matrix until the biodegradation of this one releases the active principle which will then be able to diffuse towards the outside.
  • This type of matrix delay form can be easily characterized by the penetration of water which will hydrate the dispersed zones of active principle and cause swelling of the formulation under the effect of hydration by osmotic forces, because of the impossibility of the active ingredient to escape from the matrix structure.
  • phase intermingle more or less according to the PLGA formulation, the degradation of the polymer allowing for example the increase of the size of the cavities through which the active ingredient can diffuse.
  • Polyanhydrides are, for example, polymers whose erosion process surface gives a release profile distinct from that of the PLGA and more dependent on the form of the deposit than the PLGA which undergoes an overall degradation.
  • formulations consisting of a matrix less likely to isolate the active ingredient from the medium or more quickly eliminated, generally contain a small percentage of active ingredient.
  • injectable excipients such as mannitol, polyethylene glycols, hyaluronic acid are also used, more often as additives to adjust the delay profile.
  • a certain amount of active ingredient is found on the surface of the formulation and is not included in the polymer matrix.
  • the surface active ingredient represents a high relative amount relative to the total active ingredient because of the importance of the surface relative to the total volume.
  • the release time depends directly on the degradation time of the PLGA (second phase or rebound).
  • the PLGA according to the desired duration. For example, 50:50 PLGAs, depolymerized in one month, will be used to make a formulation a month whereas necessarily three-month formulations will involve PLGAs whose hydrolysis is later, for example, 75:25 PLGA.
  • the excipient in particular PLGA, does not influence the release and it is possible, for example, to obtain three-month releases with a single 50:50 PLGA which disappears completely from the body in 60 days or forms one month with a PLGA 75:25 which has not yet begun its hydrolysis while all the active ingredient will be released.
  • the proportion of PLGA is always lower in weight than the proportion of active ingredient; which means that the continuous matrix is no longer the PLGA but the active ingredient that will thus undergo for the entire load, the external influence and in particular aqueous. It is therefore the active ingredient, in particular by the total quantity, which will determine the duration of action.
  • the invention thus also particularly relates to such formulations, whether systemically or for local treatment, with a conventional dosage or decreased for local action.
  • the invention more particularly relates to a delay formulation for parenteral administration comprising a homogeneous mixture of an active ingredient in the non-dispersed state forming a continuous phase, at least a portion of which is in direct contact with the exchange surface of the formulation and external biological medium, and a biodegradable biocompatible excipient, wherein the amount of active ingredient is at least 50% by weight relative to the total weight of the formulation, and having a release profile that is independent of the composition of the excipient of the molecular weight of the excipient or the active ingredient / excipient weight ratio, the release profile being essentially exclusively dependent on the total amount of active ingredient present in the formulation.
  • the formulations of the invention contain more than 50% of active principle, which represents a decrease in the volume of the deposit of the order of 3 to 10 times compared to the volume of the matrix forms.
  • the formulations of the invention advantageously contain, before and after deposition, at least 50%, preferably at least 51%, advantageously at least 60% and more advantageously at least 70% and up to 99.999% by weight relative to the total weight of the formulation, excipient representing less than 50%, preferably less than 49%, and more preferably less than 30% by weight based on the total weight of the formulation.
  • the excipients are those conventionally used in solid delayed release forms, especially biodegradable polymers.
  • polylactic or polyglycolic acid type polymers or polylactic-polyglycolic acid type copolymers, or mixtures of these polymers and / or copolymers.
  • biodegradable biocompatible polymer forming the excipient is indifferent, the latter having no influence on the diffusion capacity of the active ingredient in the polymer.
  • an injectable fatty substance may be used as excipient of the formulations of the invention, such as a polymerized or saturated fatty acid such as ®Compritol or else excipients such as polyvinylpyrrolidone (PVP) or polyethylene glycol (PEG).
  • a polymerized or saturated fatty acid such as ®Compritol
  • excipients such as polyvinylpyrrolidone (PVP) or polyethylene glycol (PEG).
  • the viscosity of the polymers can vary considerably. It has been shown that polymers of low viscosity may be suitable for a mode of release called monophasic active principle. Licences EP 58481 and 52510 mentioned above, but also patents EP 21234 and EP 26599 for example, have focused on low viscosity polymers. These polymers may be suitable for the present invention (e.g., viscosity less than 0.5 dl / g in chloroform).
  • DL-PLGA or L-PLGA can be used, more preferably DL-PLGA made from 70 to 80% DL-lactide and 20 to 30% glycolide.
  • PLGA synthesized from 75% DL-lactide to 25% glycolide is particularly suitable, but other copolymers including PLGA 50-50 can also be used.
  • D or DL-lactide polymers can also be used.
  • PLGAs can be hydrophilic or hydrophobic.
  • the formulations of the invention can be made with hydrophilic polymers.
  • PLGA is preferred, in particular a hydrophilic PLGA advantageously having a viscosity in chloroform at 1 g / 100 ml greater than 0.6 dl / g.
  • the duration of action of the delay formulation will be determined exclusively by the total amount of active ingredient that it contains.
  • active ingredient in the undispersed state it is meant that the various active ingredient particles present in the formulation are in majority physically in contact with each other and up to the surface of the formulation.
  • continuous phase is meant a distribution such that all or most of the inner parts of the active principle are separated from the surface only by the active principle or a mixture of active principle and a substance that does not oppose not to diffusion or dissolution of the active ingredient.
  • the mixture formed by the active ingredient and the excipient is in all respects homogeneous.
  • the delay formulations according to the invention are further characterized by their difference in the release time in vitro and in vivo.
  • the formulations according to the invention placed in a physiological aqueous medium release the active ingredient over a period of less than seven days whereas the duration of action in vivo is substantially greater than this period, advantageously at least one month, and preferably at least three months.
  • Matrix formulations comprising the same amount of active ingredient on the other hand had a longer in vitro release, of the same order of magnitude as the release time in vivo.
  • the formulations according to the invention make it possible to obtain, in vivo, a much greater release time without any relation to the in vitro release time .
  • the in vivo release profile is clearly different from that of the two-phase matrix forms and will be pseudo-order 0, corresponding to a constant diffusion of the active ingredient over time.
  • This release profile is another advantage since it allows a release of active ingredient of a constant level in the body.
  • formulations according to the invention are injected directly in their solid form in the absence of any liquid excipient; the high proportion of active ingredient is therefore a decisive advantage, allowing to reduce the volume significantly.
  • the new formulations according to the invention with, for example, 70% of active principle make it possible to reduce the volume by a factor of 3.5 or to multiply the dose by 3.5 for an identical volume.
  • a standard intramuscular needle is sufficient to deposit a microimplant.
  • a formulation according to the invention having less than 1 mm in diameter.
  • the mode of release of the formulation of the invention without absorption of fluids, nor initial swelling of a matrix, constitutes a stability advantage for the active ingredient which is preserved in a controlled environment.
  • the delay forms, according to the invention are therefore particularly advantageous for fragile active ingredients such as recombinant proteins.
  • the invention thus allows the prolonged release of fragile molecules, especially peptides and proteins, or their analogs.
  • proteins chosen for example from the group consisting of Triptorelin acetate, lanreotide acetate, of a compound having LH-RH activity such as that Triptorelin, goserelin, leuprorelin, buserelin or their salts, an LH-RH antagonist, a GPllb / IIIa antagonist, a compound having a similar activity to a GPIIb / IIIa antagonist, erythropoietin (EPO) or one of its analogues, the various interferons ⁇ , interferon ⁇ or ⁇ , somatostatin, a derivative of somatostatin as described in the European patent EP 215171 , a somatostatin analogue as described in the US Pat.
  • LH-RH activity such as that Triptorelin, goserelin, leuprorelin, buserelin or their salts
  • an LH-RH antagonist a GPllb / IIIa antagonist
  • a water-soluble product obtained by salification in the form of a cation, with, for example, acetic acid.
  • an insoluble salt such as pamoate can be used.
  • peptide and / or protein is meant both the peptide and / or the protein themselves as fragments of these peptides or proteins pharmacologically active.
  • the water-soluble active substance as used to manufacture the formulations or implants according to the invention may be in particular Triptorelin acetate, lanreotide acetate, goserelin, leuprorelin, buserelin or their salts.
  • formulations also have the advantage that they can be administered by using the above device for the process according to the invention.
  • the methods for manufacturing the formulations according to the invention are based on mixing techniques, compression techniques, melt extrusion techniques and molding techniques, conventionally used in the field of the manufacture of galenic retardation forms.
  • This operation aims to improve the quality of the powder mixture flow during the extrusion required in this particular situation where the melted portion represents less than 50% of the total.
  • the mixture is extruded through a die of the same diameter as the microimplants desired.
  • the extrudate is recovered after checking the diameter by laser beams (Keyence) on a drawing track.
  • the microimplants are calibrated by the extrusion nozzle and not by stretching.
  • the extrudate is cut to the desired length depending on the analytical control to obtain the microimplants which are then loaded into the injection devices before gamma irradiation (25 kGy).
  • This hypercompression can be obtained with a minimum force of one ton.
  • thermoplastic excipient capable of melting at temperature
  • This operation takes place at room temperature, cold or even below 0 ° C. During this hypercompression, the glass transition to the plastic state of the excipient within the mixture is obtained at a lower temperature.
  • This technique which is particularly suitable for PLGA retarding forms, makes it possible, without temperature, solvent or manufacturing vehicles, to obtain galenic forms which are particularly advantageous for preserving the integrity of the active ingredient, in particular for fragile molecules such as, for example, proteins. recombinant.
  • This method is also advantageous for the manufacture of matrix forms (comprising not more than 50% of active ingredient) that they are dispersed or not dispersed.
  • matrix forms comprising not more than 50% of active ingredient
  • the compression of the PLGA leads to a matrix structure equivalent to that obtained by melting the excipient while hot.
  • the hyper-tablets after grinding can be used directly in a dispersed form of microparticles.
  • the dispersed form can be injected directly after loading into a needle of a device as described above or be injected in suspension in a liquid medium (as for the microspheres, for example).
  • One of the possible aspects for the solid form is that of an elongated cylinder.
  • the formulation as defined above may, preferably, have the shapes and dimensions defined above in relation to the local administration device described.
  • the formulation is in the form of a cylinder with a diameter of less than 3 mm, preferably less than 1 mm and a length of less than 50 mm, preferably less than 30 mm, the total volume being less than 50 mm 3 , preferably at 20 mm 3 .
  • the invention also relates to a method of therapeutic treatment comprising the injection to a patient requiring a treatment involving the release of an active ingredient over a prolonged period of a formulation according to the invention.
  • the formulation can be advantageously injected subcutaneously or intramuscularly.
  • the invention also relates to the use of a solid formulation as defined above for obtaining a delay effect.
  • a batch it is possible, for example, to weigh 38.25 g of lactide-coglycolide copolymer PLGA (50:50) and to incorporate 6.75 g of dexamethasone-21-disodium phosphate milled to less than 100 micrometers.
  • the powder will be mixed using the three-dimensional mixer and the first extrusion, the quality of the mixture (% PA) will be checked.
  • the device can be directly used inside a trocar of 3 mm in diameter and 10 cm in length according to the diagrams of FIGS. 5 to 10.
  • a model on the rat is used.
  • the insert is administered either subcutaneously or intraperitoneally and the release over a month is evaluated by default by dosing the amount of AP remaining in the insert after sacrifice of animals and sampling at fixed times.
  • Figures 20, 21 and 22 show the results of this in-vivo control at three percentages subcutaneous (A) and intraperitoneal (B).
  • Implants or cylinders 0.75 mm in diameter and 30 mm in length were manufactured. They contain 12.80 mg of Lanreotide (BIM2301-4C) for a composition containing 90% Lanreotide Acetate and 10% Mannitol.
  • BIM2301-4C Lanreotide
  • the manufacturing comprises the following steps: weighing, connection, vacuum, hydration, mixing, extrusion, drying, setting and irradiation.
  • the weighing corresponds to the volume of the water-mannitol solution, on the one hand, in a syringe and to the Somatuline acetate powder in the other syringe.
  • connection is the combination of the two syringes via a 3-way ball valve.
  • the vacuum is then formed inside the PA powder.
  • Hydration is achieved by contacting the powder under vacuum with the Mannitol solution.
  • the mixture is made by coming and going by actuating the pistons of the two syringes.
  • the extrusion corresponds after checking the HPLC homogeneity to the production of a rod through a die adapted to the desired diameter. This extrusion is also obtained by operating with a motor the plunger of the syringe.
  • the drying is carried out after or before cutting the rolls. It consists of evaporating the water from the pasty mixture to obtain the dry cylinder.
  • the arrangement consists in introducing the cylinder inside the injection needle in a device 1 mm in diameter as shown in FIG.
  • Irradiation by sterilization, after packaging of the device, is carried out with 25 kGy.
  • This device can be injected locally to deposit the lanreotide cylinder before or after angioplasty, like a stent, by the catheter lumen.
  • Figure 23 shows the result of dog pharmacokinetics of the solid form 12.8 mg of Lanreotide intramuscular.
  • Figure 24 shows the results of kinetics in the healthy volunteer subcutaneous (A) and intramuscular (B).
  • Lanréotide acetate forms with water a paste or a semi-solid retarded injectable.
  • the delay effect is obtained by depositing directly from the active ingredient. This delay effect is adjustable according to the percentage. The duration of action is therefore directly proportional to the erosion or elimination of this semi-solid deposit. We can therefore associate any other active ingredient whose local effect combined with Lanréotide.
  • the duration of action of the AP (s) may be evaluated by the sole pharmacokinetics of Lanreotide.
  • the semi-solid is made in a process similar to that of the solid of Example 2 without Mannitol. Extrusion, drying and rearrangement are replaced by a distribution.
  • 40 g of Lanreotide Acetate will be prepared in the case of the one month 35% acetate form of Lanreotide, 65% water and for injected doses of 40 mg of AP.
  • the manufacturing steps are weighing, connection, vacuum, hydration, mixing, distribution and irradiation.
  • the distribution consists of a volumetric filling of the injection device ( Figures 11 to 16), for example, by rotary piston from the mixing syringe.
  • This semi-solid formulation has been clinically tested in healthy intramuscular volunteers ( Figure 25).
  • a very soluble salt of Triptorelin acetate (AT) is mixed with a PLGA (75:25) of more than 100,000 molecular weight and inherent viscosity equal to 1 dl / g in chloroform which undergoes loss hydrolysis. mass capable of controlling a matrix release after one month.
  • Implants with 20% of active principle release only 4% of the total dose in two days and only 6.7% in 36 days before the loss of mass of the polymer which causes the release of the active principle between J36 and J60 Figure 26. Implants with 52% active ingredient release 66% of the total dose in two days and more than 90% in one week (Figure 27).
  • Triptorelin pamoate Comparison of a matrix and non-matrix form with an insoluble salt of Triptorelin
  • Example 4 The matrix preparation of Example 4, PLGA 75:25 - Triptorelin acetate (80% -20%) in undispersed form after ten days in in vitro physiological medium contains substantially all of its active ingredient; it has a translucent appearance with an increase in diameter and a decrease in length over time 0 (FIG. 30), which demonstrates a constraint of the PLGA matrix.
  • the PLGA non-matrix preparation 75 25 - Triptorelin acetate (48% -52%) under the same conditions after ten days, is virtually completely emptied of active ingredient. It did not change in diameter or length ( Figure 31).
  • the active ingredient has escaped from the non-matrix skeleton PLGA.
  • the active ingredient is free of any physicochemical stress with the polymer.
  • the PLGA remains unchanged during the release of the active ingredient.
  • Figure 35 shows the evolution of the residual amount of pure active ingredient in mg. It is noted that contrary to the in vitro results after 19 days, there remains on average a significant amount of active ingredient and equivalent in implants at 52% and in implants at 70% and 80%.
  • the 20% Triptorelin acetate and 52% formulations were injected IM in two sets to six dogs at total doses of 3 and 6 mg of pure triptorelin and the kinetics by RIA analysis of the plasma samples and the dynamic efficiency of the active ingredient with the testosterone levels (FIGS. 36 and 37).
  • the results show a release activity over at least three months in both cases.
  • the kinetics of the shape at 20% shows a classic profile (with peak and rebound).
  • the kinetics of the 52% form is not comparable to those of conventional PLGA forms but pseudo 0 order without peak or rebound.
  • EXAMPLE 11 Pharmacokinetic results of a non-matrix formulation with 70% of active principle on the dog.
  • a formulation using the same PLGA and the same active ingredient as the 52% active ingredient formulation (Example 10) was carried out with 70% and 30% PLGA.
  • This formulation was injected IM in dogs at the total dose of 9 mg of pure triptorelin.
  • the kinetics were monitored by RIA analysis of the plasma samples (FIG. 38A) as well as the dynamic efficiency of the active ingredient with testosterone levels (FIG. 38B).

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Claims (46)

  1. System zur Implantation und Insertion einer festen Formulierung (1, 9) oder halbfesten Formulierung (18) an eine genau definierte Depotstelle des Organismus, so dass sie während einer bestimmten Zeitdauer an der Stelle verbleiben kann, wobei die Formulierung wenigstens einen Wirkstoff enthält und das System:
    eine erste invasive Vorrichtung (6, 7, 11, 50) umfasst, um zur Depotstelle zu gelangen;
    und eine sich von der ersten unterscheidende zweite Vorrichtung umfasst, welche einen Teil besitzt, der dazu bestimmt ist, mit festen oder halbfesten Konditionierungsmitteln ins Innere des Körpers des Patienten platziert zu werden, Mittel zur Positionierung bis zur Depotstelle, Mittel zur Injektion oder Insertion in diese Depotstelle, Mittel zum Zurückziehen nach der Injektion oder der Insertion sowie einen auf der äusseren Seite belassenen Teil mit Mitteln zur Aktivierung von Funktionen der Vorrichtung;
    wobei die zweite Vorrichtung (2, 3, 13, 14) eine derart feine und langgezogene Form aufweist, dass sie in der ersten invasiven Vorrichtung positioniert und von dieser aus aktiviert werden kann, um die feste oder halbfeste Formulierung, die in den Konditionierungsmitteln enthalten ist, an der Stelle zu deponieren.
  2. System nach Anspruch 1, dadurch gekennzeichnet, dass die erste Vorrichtung ein Trokar ist.
  3. System nach Anspruch 1, dadurch gekennzeichnet, dass die erste Vorrichtung ein Katheter ist.
  4. System nach Anspruch 1, dadurch gekennzeichnet, dass die erste Vorrichtung ein Endoskop ist.
  5. System nach Anspruch 1, dadurch gekennzeichnet, dass die erste Vorrichtung ein Instrument ist, welches für eine in erster Linie chirurgische Route angepasst ist.
  6. System nach einem der Ansprüche 1 bis 5, dadurch gekennzeichnet, dass die Formulierung eine retardierte Formulierung ist.
  7. System nach einem der Ansprüche 1 bis 6, dadurch gekennzeichnet, dass die Formulierung eine niedrige Dosis an Wirkstoff im Verhältnis zu der für eine Behandlung über den systemischen Weg gewöhnlichen Dosis des entsprechenden Wirkstoffs enthält.
  8. System nach einem der Ansprüche 1 bis 7, dadurch gekennzeichnet, dass die Formulierung eine feine und langgezogene Form, insbesondere eine zylindrische Form aufweist.
  9. System nach Anspruch 8, dadurch gekennzeichnet, dass die Formulierung einen Durchmesser zwischen 0,1 und 2 bis 3 mm aufweist.
  10. System nach einem der Ansprüche 8 und 9, dadurch gekennzeichnet, dass die Formulierung ein Mindestverhältnis Länge/Durchmesser von 10 aufweist.
  11. System nach einem der Ansprüche 6 bis 10, dadurch gekennzeichnet, dass die Formulierung natürlicherweise fest ist und, indem es in der Vorrichtung vorgespannt ist, deformiert werden kann, um in situ ihre Form anzunehmen.
  12. System nach einem der Ansprüche 1 bis 11, dadurch gekennzeichnet, dass die Formulierung in den Konditionierungsmitteln vorgespannt ist und eine nicht-geradlinige Form aufweist, wenn es in ihrer Depotstelle platziert ist.
  13. System nach einem der Ansprüche 6 bis 12, in welchem die Länge und der Durchmesser der Formulierung so gewählt sind, um ihre Eliminierung oder ihre Verschiebung zu vermeiden.
  14. System nach einem der Ansprüche 7 bis 13, dadurch gekennzeichnet, dass die Formulierung und der Wirkstoff, welchen diese enthält, so gewählt sind, dass die Abgabe des Wirkstoffs in den Sekretionen einer Schleimhaut einer Körperhöhle stattfindet.
  15. System nach Anspruch 14 in welchem die Körperhöhle oder Schleimhaut eine Körperhöhle oder Schleimhaut des Gesichts- oder des ORL-Bereichs ist.
  16. System nach Anspruch 14, in der die Schleimhaut eine tracheo-pulmonale Schleimhaut ist.
  17. System nach Anspruch 14, in der die Schleimhaut die bukkal-oesophageale Schleimhaut ist.
  18. System nach einem der Ansprüche 14 bis 17, in welcher die Formulierung angeordnet ist, um an der Oberfläche der besagten Schleimhaut in einer Art platziert zu werden, dass der Wirkstoff durch den Schleim transportiert wird.
  19. System nach einem der Ansprüche 6 bis 18, dadurch gekennzeichnet, dass die Formulierung ein für die Behandlung naso-sinusialer Polypose, allergischer oder nicht-allergischer Nasenschleimhautentzündungen, nicht-infektiöser Mittelohrenentzündungen oder Nasennebenhöhlenentzündungen angepasstes Corticoid enthält.
  20. System nach einem der Ansprüche 1 bis 18, dadurch gekennzeichnet, dass die Formulierung einen entzündungshemmenden Wirkstoff enthält.
  21. System nach einem der Ansprüche 1 bis 20, dadurch gekennzeichnet, dass die Formulierung eine hohe Konzentration an Wirkstoff im Bereich zwischen 20 und 100% enthält.
  22. System nach Anspruch 21, gekennzeichnet durch eine Konzentration an Wirkstoff im Bereich zwischen 40 und 100%.
  23. System nach Anspruch 22, gekennzeichnet durch eine Konzentration an Wirkstoff im Bereich zwischen 50 und 100%.
  24. System nach einem der Ansprüche 7 bis 23, dadurch gekennzeichnet, dass der Wirkstoff an eine copolymere Polylaktidglykolid (PLGA)-Trägersubstanz gebunden ist.
  25. System nach einem der Ansprüche 6 bis 24, dadurch gekennzeichnet, dass es einen Wirkstoff auf Basis eines Peptids oder Proteins enthält.
  26. System nach einem der Ansprüche 6 bis 25, dadurch gekennzeichnet, dass die Formulierung eine retardierte Formulierung ist, indem es mindestens einen Wirkstoff und eine bioabbaubare Trägersubstanz aufweist, wobei die Trägersubstanz ein copolymeres Polylaktidglykolid (PLGA) ist, und die Konzentration des Wirkstoffs im Bereich zwischen 40 und 100% liegt.
  27. System nach Anspruch 26, dadurch gekennzeichnet, dass die Konzentration des Wirkstoffs im Bereich zwischen 50 und 100% liegt.
  28. System nach einem der Ansprüche 26 und 27, dadurch gekennzeichnet, dass die Formulierung eine feine und langgezogene Form mit einem Durchmesser von höchstens 3 mm aufweist.
  29. System nach Anspruch 28, dadurch gekennzeichnet, dass die Formulierung einen Durchmesser von höchstens 2 mm aufweist.
  30. System nach Anspruch 28, dadurch gekennzeichnet, dass die Formulierung einen Durchmesser in der Grössenordnung von 0,1 mm aufweist.
  31. System nach einem der Ansprüche 26 bis 30, dadurch gekennzeichnet, dass die Formulierung ein Mindestverhältnis Länge/Durchmesser von 10 aufweist.
  32. System nach einem der Ansprüche 26 bis 31, dadurch gekennzeichnet, dass die feste retardierte Formulierung zur parenteralen Verabreichung eine homogene Mischung eines Wirkstoffs im nicht dispergierten Zustand, welcher eine kontinuierliche Phase bildet, von der wenigstens ein Teil in direktem Kontakt mit der Austauschoberfläche der Formulierung und der äusseren biologischen Umgebung steht, und einer biokompatiblen bioabbaubaren Trägersubstanz enthält, in welcher die Menge an aktivem Mittel höher als 50 Gew.-% bezogen auf das Gesamtgewicht der Formulierung vorliegt, und ein von der Zusammensetzung der Trägersubstanz, dem Molekulargewicht der Trägersubstanz oder vom Gewichtsverhältnis Wirkstoff/Trägersubstanz unabhängiges Abgabeprofil aufweist, wobei das Abgabeprofil im Wesentlichen ausschliesslich von der Gesamtmenge des in der Formulierung vorliegenden Wirkstoffs abhängig ist.
  33. System nach Anspruch 32, dadurch gekennzeichnet, dass die biokompatible bioabbaubare Trägersubstanz ein Polymer oder Copolymer von Milchsäure und/oder Glykolsäure oder eine Mischung von Polymeren und/oder Copolymeren von Milchsäure und/oder Glykolsäure ist.
  34. System nach Anspruch 33, dadurch gekennzeichnet, dass das biokompatible bioabbaubare Polymer ein Copolymer von Milchsäure und Glykolsäure (PLGA) ist.
  35. System nach einem der Ansprüche 32 bis 34, dadurch gekennzeichnet, dass das biokompatible bioabbaubare Polymer ein Copolymer von Milchsäure und Glykolsäure ist, wobei 1 g in 100 ml Chloroform eine intrinsische Viskosität höher als 0,6 dl/g aufweist.
  36. Zusammensetzung nach Anspruch 34 oder 35, dadurch gekennzeichnet, dass das Copolymer ais Milchsäure und Glykolsäure hydrophil ist.
  37. System nach einem der Ansprüche 32 bis 35, dadurch gekennzeichnet, dass es, wenn es in vitro in eine flüssige physiologische Umgebung freigesetzt wird, im Wesentlichen das gesamte aktive Mittel in wenigstens einer Woche freisetzt und, wenn es in vivo subkutan oder intramuskulär verabreicht wird, eine Abgabe des Wirkstoffs während einer Zeitspanne von wesentlich länger als einer Woche aufzeigt.
  38. System nach einem der Ansprüche 32 bis 37, dadurch gekennzeichnet, dass es eine vollständig homogene Mischung des Wirkstoffs und der Trägersubstanz umfasst.
  39. System nach irgendeinem der Ansprüche 32 bis 38, dadurch gekennzeichnet, dass die Abgabe in einer einzigen Diffusionsphase des Wirkstoffs stattfindet.
  40. System nach irgendeinem der Ansprüche 32 bis 39, dadurch gekennzeichnet, dass der Wirkstoff wenigstens zu 51 Gew.-%, vorzugsweise wenigstens 60 Gew.-%, bevorzugt wenigstens 70% bis zu 99,999 Gew.-% bezogen auf das Gesamtgewicht der Formulierung vorliegt, wobei die Trägersubstanz zu weniger als 50 Gew.-%, bevorzugt weniger als 49 Gew.-% und bevorzugter weniger als 30 Gew.-% bezogen auf das Gesamtgewicht der Formulierung vorliegt.
  41. System nach irgendeinem der Ansprüche 32 bis 40, dadurch gekennzeichnet, dass der Wirkstoff ein Peptid, ein Peptid-Analoges oder ein Protein ist, insbesondere LHRH oder ein Analoges von LHRH, insbesondere Triptorelin.
  42. System nach irgendeinem der vorhergehenden Ansprüche, dadurch gekennzeichnet, dass die zweite Vorrichtung einen maximalen Durchmesser von 3 mm aufweist.
  43. System nach Anspruch 42, dadurch gekennzeichnet, dass die zweite Vorrichtung einen Durchmesser geringer als 2,5 mm aufweist.
  44. System nach Anspruch 42, dadurch gekennzeichnet, dass die zweite Vorrichtung einen Durchmesser von weniger als 2 mm aufweist.
  45. System nach irgendeinem der Ansprüche 6 bis 44, dadurch gekennzeichnet, dass die Formulierung einen Wirkstoff zur lokalen Wirkung umfasst.
  46. System nach Anspruch 6, dadurch gekennzeichnet, dass die Formulierung Dexamethason in einer Konzentration im Bereich zwischen 10 und 20% enthält.
EP97948983A 1996-12-02 1997-12-02 Vorrichtung zur lokalen verabreichung von fest-oder halbfesten pharmazeutischen zusammensetzungen Expired - Lifetime EP0952867B1 (de)

Priority Applications (1)

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EP01118964A EP1159957A3 (de) 1996-12-02 1997-12-02 Vorrichtung zur lokalen Verabreichung fester oder halbfester Formulierungen, Retardformulierungen zur parenteralen Verabreichung sowie Herstellungsverfahren

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
FR9614755 1996-12-02
FR9614755A FR2756493B1 (fr) 1996-12-02 1996-12-02 Dispositif d'administration locale de formulations solides ou semi-solides
PCT/FR1997/002182 WO1998024504A2 (fr) 1996-12-02 1997-12-02 Dispositif d'administration locale de formulations pharmaceutiques solides ou semi-solides, formulations pharmaceutiques retard pour l'administration parenterale et procede de preparation

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EP01118964A Division EP1159957A3 (de) 1996-12-02 1997-12-02 Vorrichtung zur lokalen Verabreichung fester oder halbfester Formulierungen, Retardformulierungen zur parenteralen Verabreichung sowie Herstellungsverfahren

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EP0952867B1 true EP0952867B1 (de) 2007-08-22

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EP01118964A Withdrawn EP1159957A3 (de) 1996-12-02 1997-12-02 Vorrichtung zur lokalen Verabreichung fester oder halbfester Formulierungen, Retardformulierungen zur parenteralen Verabreichung sowie Herstellungsverfahren

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PL194894B1 (pl) 2007-07-31
IL130211A0 (en) 2000-06-01
CA2273017C (fr) 2008-09-16
CA2273017A1 (fr) 1998-06-11
DE69738048D1 (de) 2007-10-04
KR20000069264A (ko) 2000-11-25
RU2207845C2 (ru) 2003-07-10
CN1244132A (zh) 2000-02-09
CZ191999A3 (cs) 2000-03-15
KR100483447B1 (ko) 2005-04-14
JP5138537B2 (ja) 2013-02-06
BR9713675A (pt) 2000-03-28
WO1998024504A3 (fr) 1998-08-06
NO332358B1 (no) 2012-09-03
DE69738048T2 (de) 2008-05-15
FR2756493B1 (fr) 2001-04-13
EP0952867A2 (de) 1999-11-03
ES2290971T3 (es) 2008-02-16
CN1210080C (zh) 2005-07-13
PT952867E (pt) 2007-12-10
ATE370764T1 (de) 2007-09-15
EP1159957A2 (de) 2001-12-05
HU228236B1 (en) 2013-02-28
AU742061B2 (en) 2001-12-13
IL130211A (en) 2006-12-31
NO992610L (no) 1999-08-02
AU7623298A (en) 1998-06-29
NO992610D0 (no) 1999-05-31
JP2001506144A (ja) 2001-05-15
JP2009018196A (ja) 2009-01-29
CN1698580A (zh) 2005-11-23
HUP9904601A3 (en) 2001-03-28
EP1159957A3 (de) 2003-06-04
FR2756493A1 (fr) 1998-06-05
WO1998024504A2 (fr) 1998-06-11
HUP9904601A2 (hu) 2000-10-28
DK0952867T3 (da) 2007-11-05
CZ301103B6 (cs) 2009-11-11
NZ336074A (en) 2001-10-26

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